System and method for ablation procedure monitoring using electrodes

ABSTRACT

A microwave ablation system includes an antenna assembly configured to deliver microwave energy from a power source to tissue. One or more electrodes are disposed on the antenna assembly and are configured to be positioned relative to tissue upon insertion of the antenna assembly into tissue. The one or more electrodes are configured to generate a feedback signal in response to an electrical signal supplied thereto from the power source. The feedback signal corresponds to the proximity of tissue relative to the at least one electrode and is configured to be compared to a predetermined parameter to determine a depth of the insertion of the antenna assembly into tissue. The power source is configured to control the delivery of microwave energy to the antenna assembly based on the comparison.

BACKGROUND

1. Technical Field

The present disclosure relates to apparatus and methods for providing energy to tissue and, more particularly, to electromagnetic radiation delivery procedures utilizing ablation probes and methods of monitoring an ablation procedure using electrodes.

2. Discussion of Related Art

Treatment of certain diseases requires destruction of malignant tumors. Electromagnetic radiation can be used to heat and destroy tumor cells. Treatment may involve inserting ablation probes into tissues where cancerous tumors have been identified. Once the probes are positioned, electromagnetic energy is passed through the probes into surrounding tissue.

In the treatment of diseases such as cancer, certain types of cancer cells have been found to denature at elevated temperatures that are slightly lower than temperatures normally injurious to healthy cells. Known treatment methods, such as hyperthermia therapy, use electromagnetic radiation to heat diseased cells to temperatures above 41° C. while maintaining adjacent healthy cells below the temperature at which irreversible cell destruction occurs. These methods involve applying electromagnetic radiation to heat, ablate and/or coagulate tissue. Microwave energy is sometimes utilized to perform these methods. Other procedures utilizing electromagnetic radiation to heat tissue also include coagulation, cutting and/or ablation of tissue.

Electrosurgical devices utilizing electromagnetic radiation have been developed for a variety of uses and applications. A number of devices are available that can be used to provide high bursts of energy for short periods of time to achieve cutting and coagulative effects on various tissues. There are a number of different types of instruments that can be used to perform ablation procedures. Typically, microwave instruments for use in ablation procedures include a microwave generator, which functions as an energy source, and a microwave surgical instrument having an antenna assembly for directing the energy to the target tissue. The microwave generator and surgical instrument are typically operatively coupled by a cable assembly having a plurality of conductors for transmitting microwave energy from the generator to the instrument, and for communicating control, feedback and identification signals between the instrument and the generator.

Microwave energy is typically applied via antenna assemblies that can penetrate tissue. Several types of antenna assemblies are known, such as monopole and dipole antenna assemblies. In monopole and dipole antenna assemblies, microwave energy generally radiates perpendicularly away from the axis of the conductor. A monopole antenna assembly includes a single, elongated conductor that transmits microwave energy. A typical dipole antenna assembly has two elongated conductors, which are linearly aligned and positioned end-to-end relative to one another with an electrical insulator placed therebetween. Each conductor may be about ¼ of the length of a wavelength of the microwave energy, making the aggregate length of the two conductors about ½ of the wavelength of the supplied microwave energy. During certain procedures, it can be difficult to assess the extent to which the microwave energy radiates into the surrounding tissue, making it difficult to determine the area or volume of surrounding tissue that will be or is ablated.

During operation, microwave antenna assemblies radiate microwave fields that, when the antenna assembly is used properly, are used therapeutically. However, when a microwave antenna assembly is not used properly, the radiated microwave fields may pose a hazard to both the patient and the user of the antenna assembly. Improper use of an antenna assembly, for example, may include insufficient insertion depth of the shaft of the antenna assembly into tissue. In this scenario, if the antenna assembly is not inserted to the minimum depth required for proper operation, microwave fields may undesirably propagate along the shaft toward the user.

SUMMARY

According to an embodiment of the present disclosure, a microwave ablation system includes an antenna assembly configured to deliver microwave energy from a power source to tissue. One or more electrodes are disposed on the antenna assembly and are configured to be positioned relative to tissue upon insertion of the antenna assembly into tissue. The one or more electrodes are configured to generate a feedback signal in response to an electrical signal supplied thereto from the power source. The feedback signal corresponds to the proximity of tissue relative to the at least one electrode and is configured to be compared to a predetermined parameter to determine a depth of the insertion of the antenna assembly into tissue. The power source is configured to control the delivery of microwave energy to the antenna assembly based on the comparison.

According to another embodiment of the present disclosure, a method of performing a tissue ablation procedure includes the steps of inserting an antenna assembly into tissue and generating an electrical signal from a power source to at least one electrode disposed on the antenna assembly. The method also includes the step of generating a feedback signal in response to the electrical signal. The feedback signal depends on the proximity of tissue relative to the at least one electrode. The method also includes the steps of comparing the feedback signal to a predetermined parameter and determining an insertion depth of the antenna assembly relative to tissue based on the comparison. The method also includes the step of controlling delivery of energy from the power source to the antenna assembly for application to tissue based on the comparison.

According to another embodiment of the present disclosure, a microwave antenna assembly includes an antenna configured to deliver microwave energy to tissue. The antenna includes an inner conductor, an outer conductor and an inner insulator disposed therebetween. One or more electrodes are disposed on the antenna and are configured to be positioned relative to tissue upon insertion of the antenna into tissue. The one or more electrodes are configured to receive an electrical signal and generate a feedback signal in response to the received signal. The feedback signal corresponds to the proximity of tissue relative to the at least one electrode and the feedback signal is configured to be compared to one or more predetermined parameters to determine a depth of the insertion of the antenna into tissue. The delivery of microwave energy from the antenna to tissue is based on the comparison.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 shows a diagram of a microwave antenna assembly in accordance with an embodiment of the present disclosure;

FIG. 2A shows a perspective view of a distal end of the microwave antenna assembly of FIG. 1;

FIG. 2B shows a side view of a distal end of the microwave antenna assembly of FIG. 1;

FIG. 3 shows a system block diagram of a microwave antenna assembly according to another embodiment of the present disclosure;

FIG. 4A shows a distal end of the microwave antenna assembly of FIG. 3 according to another embodiment of the present disclosure;

FIG. 4B shows a pair of electrodes separated from the microwave antenna assembly of FIG. 4A;

FIG. 5A shows a distal end of the microwave antenna assembly of FIG. 3 according to another embodiment of the present disclosure;

FIG. 5B shows a pair of electrodes separated from the microwave antenna assembly of FIG. 5A;

FIG. 6A shows a distal end of the microwave antenna assembly of FIG. 3 according to another embodiment of the present disclosure;

FIG. 6B shows a pair of electrodes separated from the microwave antenna assembly of FIG. 6A;

FIG. 7A shows a distal end of the microwave antenna assembly of FIG. 3 according to another embodiment of the present disclosure;

FIG. 7B shows an electrode separated from the microwave antenna assembly of FIG. 7A;

FIG. 8A shows a distal end of the microwave antenna assembly of FIG. 3 according to another embodiment of the present disclosure;

FIG. 8B shows a pair of electrodes separated from the microwave antenna assembly of FIG. 8A; and

FIG. 9 shows a distal end of the microwave antenna assembly of FIG. 3 according to another embodiment of the present disclosure.

DETAILED DESCRIPTION

Embodiments of the presently disclosed apparatus are described in detail below with reference to the drawings wherein like reference numerals identify similar or identical elements in each of the several views. In the discussion that follows, the term “proximal” will refer to the portion of a structure that is closer to a user, while the term “distal” will refer to the portion of the structure that is farther from the user.

Generally, the present disclosure is directed to a microwave antenna assembly having an energy source or generator adapted to deliver energy to tissue via the antenna assembly. More particularly, the present disclosure is directed to monitoring insertion depth of the microwave antenna assembly into tissue and controlling the delivery of energy from the energy source based on the monitored insertion depth.

In some embodiments, two or more bipolar electrodes are operably coupled to the antenna assembly and an associated energy source. The energy source supplies electrical energy (e.g., RF energy) to each bipolar electrode in a bipolar manner to elicit a measurable response (e.g., impedance, capacitance, inductance, etc.) that varies depending on whether tissue is present at or between the bipolar electrodes. As such, the bipolar electrodes may be strategically disposed on the antenna assembly at a predetermined location such that as the antenna assembly travels distally into tissue and, likewise, as tissue travels proximally along the longitudinal length of the antenna assembly to reach the proximity of the bipolar electrodes, the elicited response at the bipolar electrodes detectably changes relative to when tissue is absent from the proximity of the bipolar electrodes. The difference in the elicited response between the presence and non-presence of tissue at or between the bipolar electrodes is detected by the energy source and interpreted in accordance with predetermined data (e.g., a range of impedance values, capacitance values, and/or inductance values) to determine whether the insertion depth of the antenna assembly is adequate or inadequate. As explained in detail below, the output of the energy source (e.g., microwave energy) is controlled in accordance with this determination.

In some embodiments, one or more monopolar electrodes may be operably coupled to the antenna assembly and an associated energy source. The energy source supplies electrical energy (e.g., RF energy) to the monopolar electrode(s) in a monopolar manner to elicit a measurable response (e.g., impedance, capacitance, inductance, etc.) that varies depending on whether tissue is present at the monopolar electrode(s).

Hereinafter, embodiments of the presently disclosed tissue ablation systems are described with reference to the accompanying drawings. Like reference numerals may refer to similar or identical elements throughout the description of the figures. As used herein, the term “microwave” generally refers to electromagnetic waves in the frequency range of 300 megahertz (MHz) (3×108 cycles/second) to 300 gigahertz (GHz) (3×1011 cycles/second). As used herein, the phrase “transmission line” generally refers to any transmission medium that can be used for the propagation of signals from one point to another.

Various embodiments of the present disclosure provide electrosurgical systems for treating tissue and methods of controlling the delivery of electromagnetic radiation to tissue. Embodiments may be implemented using electromagnetic radiation at microwave frequencies or at other frequencies. Electrosurgical systems for treating tissue, according to various embodiments of the present disclosure, deliver microwave power to a plurality of electrosurgical devices. Electrosurgical devices, such as ablation probes, for implementing embodiments of the present disclosure may be inserted directly into tissue, inserted through a lumen, such as a vein, needle or catheter, placed into the body during surgery by a clinician, or positioned in the body by other suitable methods.

FIG. 1 shows a microwave ablation system 10 that includes a microwave antenna assembly 12 coupled to a microwave generator 14 via a flexible coaxial cable 16. The generator 14 is configured to provide microwave energy at an operational frequency from about 300 MHz to about 10,000 MHz, although other suitable frequencies are also contemplated.

In the illustrated embodiment, the antenna assembly 12 includes a radiating portion 18 connected by feedline 20 (or shaft) to the cable 16. More specifically, the antenna assembly 12 is coupled to the cable 16 through a connection hub 22 having an outlet fluid port 30 and an inlet fluid port 32 that are connected in fluid communication with a sheath 38. The sheath 38 encloses radiating portion 18 and feedline 20 to form a chamber 89 (FIG. 2) allowing a coolant fluid 37 to circulate from port 32 around the antenna assembly 12 to port 30. The ports 30 and 32 are also coupled to a supply pump 34 via supply lines 88 and 86, respectively. Supply pump 34 is, in turn, fluidly coupled to a supply tank 36. The supply pump 34 may be a peristaltic pump or any other suitable type. The supply tank 36 stores the coolant fluid 37 and, in some embodiments, may maintain the fluid at a predetermined temperature. More specifically, the supply tank 36 may include a coolant unit that cools the returning liquid from the antenna assembly 12. In another embodiment, the coolant fluid 37 may be a gas and/or a mixture of fluid and gas.

FIGS. 2A and 2B illustrate the radiating portion 18 of the antenna assembly 12 having a dipole antenna 40. The dipole antenna 40 is coupled to the feedline 20 that electrically connects antenna assembly 12 to the generator 14. As shown in FIG. 2B, the feedline 20 includes an inner conductor 50 (e.g., wire) surrounded by an insulator 52 that is, in turn, surrounded by an outer conductor 56 (e.g., a cylindrical conducting sheath). The inner and outer conductors may be constructed of copper, gold, stainless steel, or other conductive metals with similar conductivity properties. The metals may be plated with other materials, for example, other conductive materials. In one embodiment, feedline 20 may be formed from a coaxial semi-rigid or flexible cable.

The dipole antenna 40 includes a proximal portion 42 and a distal portion 44 interconnected at a feed point 46. The distal portion 44 and the proximal portion 42 may be either balanced (e.g., of equal lengths) or unbalanced (e.g., of unequal lengths). A dipole feed gap “G” is disposed between the proximal and distal portions 42 and 44 at the feed point 46. The gap “G” may be from about 1 mm to about 3 mm. In one embodiment, the gap “G” may be thereafter filled with a dielectric material at the feed point 46. The dielectric material may be polytetrafluoroethylene (PTFE), such as Teflon® sold by DuPont of Willmington, Del. In another embodiment, the gap “G” may be coated with a dielectric seal coating.

The distal portion 44 includes a conductive member 45 that may be formed from any type of conductive material, such as metals (e.g., copper, stainless steel, tin, and various alloys thereof). The distal portion 44 may have a solid structure and may be formed from solid wire (e.g., 10 AWG).

With reference to FIG. 2A, the antenna assembly 12 also includes a choke 60 disposed around the feedline 20. The choke 60 may be a quarter-wavelength shorted choke that is shorted to the feedline 20 at the proximal end (not illustrated) of the choke 60 by soldering or other suitable methods.

With continued reference to FIG. 2A, antenna assembly 12 also includes a tip 48 having a tapered end 24 that terminates, in one embodiment, at a pointed end 26 to allow for insertion into tissue with minimal resistance at a distal end of the radiating portion 18. In those cases where the radiating portion 18 is inserted into a pre-existing opening, tip 48 may be rounded or flat. The tip 48 may be formed from a variety of heat-resistant materials suitable for penetrating tissue, such as metals (e.g., stainless steel), various thermoplastic materials (e.g., poletherimide and polyamide thermoplastic resins), and ceramics (e.g., partially stabilized zirconia).

With reference to FIG. 3, a microwave ablation system, shown generally as 200, according to an embodiment of the present disclosure is depicted. The system 200 includes an ablation device 202 having a handle 205 and an antenna 203 used to ablate tissue. A microwave generator 206, which is substantially similar to generator 14 of FIG. 1, supplies the ablation device 202 with energy (e.g., microwave energy) via coaxial cable 204.

As shown in FIG. 3, a pair of electrodes 212 a and 212 b are disposed on the antenna 203 and operably coupled to a controller 216 via transmission lines 214 a and 214 b, respectively. Controller 216 may be operably coupled to the microwave generator 206, as illustrated in FIG. 3, or may be incorporated within the microwave generator 206 (not shown). Although not shown as such in FIG. 3, transmission lines 214 a and 214 b may extend proximally from electrodes 212 a and 212 b along an outer surface of the antenna 203 (e.g., via conductive tracing), and, further, through the handle 205 and cable 204 for connection to the generator 206 and/or controller 216. Electrodes 212 a and 212 b are electrically connected to the generator 206 such that generator 206 supplies electrosurgical energy (e.g., RF energy, microwave energy, etc.) to electrodes 212 a and 212 b in a bipolar configuration. More specifically, generator 206 generates energy at a first potential (e.g., “−”) to one of the electrodes (e.g., 212 a) and at a second potential (e.g., “+”) to the other electrode (e.g., 212 b). In this scenario, electrodes 212 a, 212 b are configured to conduct a suitable amount of electrosurgical energy therethrough such that a measurable response (e.g., impedance, capacitance, inductance, etc.) may be elicited from electrodes 212 a, 212 b caused by the proximity or lack of presence or lack of presence of tissue relative to the electrodes 212 a, 212 b. As described in more detail below, this measurable response varies depending on the proximity of tissue to the electrodes 212 a, 212 b. That is, the measurable response corresponding to the presence of tissue at or between the electrodes 212 a, 212 b is detectably different from the measurable response corresponding to the lack of presence of tissue at or between the electrodes 212 a, 212 b. It is this variation in the measureable response that is monitored by the controller 216 and/or generator 206 to determine whether the insertion depth of the antenna 203 relative to tissue is desired or appropriate. This determination is, in turn, utilized to control the delivery of energy from the generator 206 to the antenna 203.

When antenna 203 is not inserted into tissue to a sufficient depth, unintentional damage to surrounding tissue may occur. By monitoring the insertion depth of antenna 203 and controlling output of the generator 206 accordingly, that is, by applying energy to tissue only when antenna 203 is detected as being inserted into tissue at an appropriate depth, damage to the ablation system 200, the user, and/or the patient may be prevented. With this purpose in mind, controller 216 is configured to control the output of generator 206 based on an input signal received from one of or both of electrodes 212 a and 212 b in response to an electrical signal (e.g., RF energy) transmitted from generator 206 to electrodes 212 a, 212 b via transmission lines 214 a, 214 b, respectively. Controller 216 may be a microprocessor or any suitable logic circuit configured to receive and process an input signal from electrodes 212 a and 212 b and control output of generator 206 based on the processed input signal. Controller 216 may be operably coupled to a storage device or memory (not shown) configured to store programmable instructions, historical data, lookup tables, operating parameters, etc.

By placing electrodes 212 a and 212 b at predetermined locations along the longitudinal length of antenna 203 and relative to each other, impedance measurements of electrodes 212 a and 212 b may be utilized to monitor the insertion depth of antenna 203 relative to tissue. More specifically, the impedance of electrodes 212 a and 212 b when no tissue is present at or between electrodes 212 a and 212 b (e.g., antenna 203 is not inserted into tissue at a depth sufficient to cause tissue to be disposed at or between electrodes 212 a, 212 b) is detectably different than the impedance of electrodes 212 a and 212 b when tissue is present at or between electrodes 212 a and 212 b (e.g., antenna 203 is inserted into tissue at a depth sufficient to cause tissue to be disposed at or between electrodes 212 a, 212 b). In this manner, the detected impedance of electrodes 212 a and 212 b may be processed by the controller 216 to detect sufficient insertion depth of antenna 203 relative to tissue and, in turn, control output of generator 206 accordingly. For example, controller 216 may prevent generator 206 from supplying energy to the ablation device 202 until the antenna 203 is inserted into tissue at a sufficient depth for proper operation of device 202.

In some embodiments, one or more sensors (not shown) may be in operative communication with electrodes 212 a, 212 b and configured to provide real-time information pertaining to electrodes 212 a, 212 b to the generator 206 and/or the controller 216 via suitable transmission lines. More particularly, these sensors may be configured to provide real-time information pertaining to one or more electrical parameters (e.g., impedance, power, voltage, current, etc.), thermal parameters (e.g., temperature), etc., associated with the electrodes 212 a, 212 b. In some embodiments, the sensors may be in the form of a thermal sensor such as, for example, a thermocouple, a thermistor, an optical fiber, etc.

The sufficient insertion depth and/or the placement of electrodes 212 a and 212 b on the antenna 203 may be pre-measured and/or predetermined based on any suitable parameter such as, for example without limitation, electrode geometry, electrode spacing, antenna geometry, antenna length, a manufacturer suggested minimum insertion depth, and/or a predetermined range of sufficient insertion depths.

As discussed in further detail below, electrodes 212 a, 212 b may be configured in any number of geometries and/or lateral spacing configurations in accordance with the type of elicited response being detected to determine insertion depth. In particular, impedance measurements such as resistance and capacitance may predetermine the lateral or circumferential spacing between electrodes 212 a, 212 b as well as the geometry thereof for purposes of improving the resolution between elicited responses corresponding to the presence and lack of presence of tissue, thereby optimizing the detection of insertion depth and the overall operation of system 200.

In use, an electrical signal (e.g., RE energy) is generated by generator 206 and transmitted to electrodes 212 a and 212 b. In response, electrodes 212 a, 212 b provide an electrical feedback signal to the controller 216 that represents a real-time measurement or indication of one or more parameters pertaining to electrodes 212 a, 212 b such as impedance (e.g., capacitance, resistance, etc.). Controller 216 compares the electrical signal to a predetermined range. If the electrical signal is within the predetermined range, for example, indicating that antenna 203 is inserted into tissue at an appropriate depth, the controller 216 controls the generator 206 to supply energy to the antenna 203 for application to tissue. That is, the appropriate insertion depth of antenna 203 may be determined prior to an ablation procedure being performed such that the supply of energy to device 202 may be initiated and/or in real-time during an ablation procedure such that the application of energy to tissue may be continued. If the electrical signal is outside the predetermined range, for example, indicating that the antenna 203 is not inserted into tissue at an appropriate depth, the controller 216 controls the generator 206 to modify or terminate generator 206 output. That is, if prior to the ablation procedure being performed it is determined that antenna 203 is not inserted into tissue at an appropriate depth, controller 216 controls generator 206 to prevent the supply of energy to device 202. Likewise, if during the ablation procedure it is determined that antenna 203 is not inserted into tissue at an appropriate depth, controller 216 controls generator 206 to terminate the supply of energy to device 202. In this way, generator 206 will supply energy to antenna 203 for application to tissue only when antenna 203 is inserted into tissue at an appropriate depth as determined by the methods described hereinabove. The predetermined range may be, for example, a predetermined range of impedance values.

Each of electrodes 212 a and 212 b may be disposed anywhere along the longitudinal length of antenna 203, e.g., proximal to the radiating portion 18 (FIG. 1), and may be laterally spaced at a suitable distance from each other such that system 200 is optimized for detecting insertion depth of the antenna 203.

As described hereinabove, electrodes 212 a, 212 b may be configured in any number of geometries and/or lateral spacing configurations in accordance with the type of parameter being detected to determine insertion depth. FIGS. 4A-8 illustrate various embodiments of the ablation device 202 including bipolar electrodes that operate in conjunction with system 200 substantially as described above with respect to electrodes 212 a, 212 b to enable the detection of insertion depth of antenna 203, and are described in detail below.

With reference to FIG. 4A, a pair of laterally spaced ring electrodes 312 a, 312 b is shown operably coupled to the antenna 203 in accordance with some embodiments of the present disclosure. Electrodes 312 a and 312 b are configured to operate in conjunction with microwave ablation system 200 as substantially described above with reference to electrodes 212 a and 212 b. Electrodes 312 a and 312 b are electrically connected to generator 206 and/or controller 216 (FIG. 3) via transmission lines 314 a and 314 b, respectively, and include a lateral space 316 disposed therebetween. FIG. 4B shows the pair of electrodes 312 a, 312 b separated from antenna 203 to illustrate that electrode 312 a is generally c-shaped. In this way, when electrode 312 a is operably coupled to antenna 203, electrode 312 a does not completely encompass the circumference of antenna 203 such that transmission line 314 b is enabled to extend proximally along an outer surface of antenna 203 without interference from electrode 312 a, as illustrated in FIG. 4A. In use, when tissue is disposed within the lateral spacing 316 disposed between electrodes 312 a and 312 b, the impedance of electrodes 312 a and 312 b detectably changes from when there is air and/or no tissue disposed within the space 316.

With reference to FIG. 5A, a pair of electrodes 412 a, 412 b is shown operably coupled to antenna 203 in accordance with some embodiments of the present disclosure. Electrodes 412 a and 412 b are configured to operate in conjunction with microwave ablation system 200 as substantially described above with reference to electrodes 212 a and 212 b. Electrodes 412 a and 412 b are electrically connected to generator 206 and/or controller 216 (FIG. 3) via transmission lines 414 a and 414 b, respectively. FIG. 5B shows the pair of electrodes 412 a and 412 b separated from antenna 203 to illustrate that electrodes 412 a, 412 b are generally c-shaped or half-cylinder in shape. In this way, when electrodes 412 a, 412 b are operably coupled to antenna 203, electrodes 412 a, 412 b do not completely encompass the circumference of antenna 203 such that a space 416 is defined therebetween. In use, when tissue is disposed within the space 416 between electrodes 412 a, 412 b, the impedance of electrodes 412 a, 412 b delectably changes from when there is air and/or no tissue disposed within the space 416.

With reference to FIG. 6A, a pair of electrodes 512 a, 512 b is shown operably coupled to antenna 203 in accordance with some embodiments of the present disclosure. Electrodes 512 a and 512 b are configured to operate in conjunction with microwave ablation system 200 as substantially described above with reference to electrodes 212 a and 212 b. Electrodes 512 a and 512 h are electrically connected to generator 206 and/or controller 216 (FIG. 3) via transmission lines 414 a and 414 b, respectively. FIG. 6B shows the pair of electrodes 512 a, 512 b separated from antenna 203 to illustrate that electrodes 512 a, 512 b are generally c-shaped. Electrodes 512 a and 512 b include a plurality of laterally spaced interlocking fingers 515 a and 515 b, respectively, that define a spacing 516 between electrodes 512 a, 512 b. In operation, this interlocking or nested configuration operates to increase capacitance between electrodes 512 a, 512 b due to the close proximity of the fingers 515 a and 515 h. In this way, the resolution between elicited responses—namely, capacitance in the present scenario—corresponding to the presence and lack of presence of tissue within spacing 516 is improved, thereby optimizing the detection of insertion depth and the overall operation of system 200.

With reference to FIG. 7A, a monopolar coil electrode 612 is shown operably coupled to antenna 203 in accordance with some embodiments of the present disclosure. Electrode 612 is configured to operate in conjunction with microwave ablation system 200. Electrode 612 is electrically connected to generator 206 and/or controller 216 (FIG. 3) via a transmission line 614. Generator 206 generates energy at a single potential (e.g., either “+” or “−”) to electrode 612. In this scenario, a return electrode or return pad attached to the patient may be utilized to return the energy to the generator 206, thereby completing the circuit following from the generator 206 to the antenna 203 for application to tissue and, subsequently, back to the generator 206. FIG. 7B shows the electrode 612 separated from antenna 203 to illustrate that electrode 612 is generally helical in shape such that the electrode 612 completely encircles the circumference of antenna 203 along at least a portion of the antenna's 203 longitudinal length.

As shown in FIG. 7A, the windings of the electrode 612 define lateral spacing 616 therebetween along at least a portion of the longitudinal length of the antenna 203. Similar to electrodes 512 a, 512 b shown in FIGS. 6A and 6B, in operation, the helical configuration of electrode 612 operates to increase the electrode's 612 capacitance due to the close proximity of the helical windings thereof. In this way, the resolution between elicited responses—namely, capacitance in the present scenario—corresponding to the presence and lack of presence of tissue within spacing 616 is improved, thereby optimizing the detection of insertion depth and the overall operation of system 200.

With reference to FIG. 8A, a pair of bipolar coil electrodes 712 a, 712 b is shown operably coupled to antenna 203 in accordance with some embodiments of the present disclosure. Electrodes 712 a, 712 b are configured to operate in conjunction with microwave ablation system 200. Electrodes 712 a, 712 b are electrically connected to generator 206 and/or controller 216 (FIG. 3) via transmission lines 714 a, 714 b, respectively. Generator 206 generates energy at a first potential (e.g., “+”) to electrode 712 a and at a second potential (e.g., “−”) to electrode 712 b. FIG. 8B shows the pair of electrodes 712 a, 712 b separated from antenna 203 to illustrate that electrodes 712 a, 712 b are generally helical in shape.

As shown in FIG. 8A, the generally helical-shaped electrodes 712 a, 712 b completely encircle the circumference of antenna 203 along at least a portion of the antenna's 203 longitudinal length such that the windings of electrodes 712 a, 712 b are intertwined to define lateral spacing 716 therebetween. Similar to electrodes 512 a, 512 b shown in FIGS. 6A and 6B, in operation, the helical configuration of electrodes 712 a, 712 b operates to increase the capacitance of electrodes 712 a, 712 b due to the close proximity of the intertwined helical windings thereof. In this way, the resolution between elicited responses—namely, capacitance in the present scenario—corresponding to the presence and lack of presence of tissue within spacing 716 is improved, thereby optimizing the detection of insertion depth and the overall operation of system 200.

With reference to FIG. 9, the antenna 203, in some embodiments, may be operably associated with a trocar 245 that is configured to facilitate penetration into tissue for proper placement of the antenna 203 relative to a desired tissue site. The trocar 245 includes a hollow coaxial shaft 250 having a distal tip 258 disposed at a distal end thereof. The distal tip 258 has a generally tapered shape, e.g., conical, to facilitate the penetration thereof, and trocar 245 generally, into tissue. As shown in FIG. 9, the antenna 203 is configured to be accommodated within the hollow coaxial shaft 250 such that a distal end of the antenna 203 is operably coupled to the distal tip 258 of the trocar 245. In this scenario, the monitoring of insertion depth of antenna 203 into tissue may be accomplished by incorporating a pair of laterally spaced electrodes 712 a and 712 b disposed along the longitudinal length of the shaft 250. More specifically, and as shown by the illustrated embodiment of FIG. 9, electrode 712 b forms the distal tip 258 of the trocar 245 and is electrically connected to generator 206 and/or controller 216 (FIG. 3) via the inner conductor 50 (also see FIG. 2B) of the antenna 203.

Electrode 712 a is ring-like in shape and encircles the circumference of the shaft 250 of trocar 245 along at least a portion of the longitudinal length of the shaft 250. Electrode 712 a is laterally spaced proximally from electrode 712 b to define a space 716 therebetween. Electrode 712 a is electrically connected to generator 206 and/or controller 216 (FIG. 3) via a transmission line 714 a. As shown in the illustrated embodiment, transmission line 714 a extends proximally from electrode 712 a along an outer surface of the trocar 245. In some embodiments, although not shown, transmission line 714 a may be connected through the shaft 250 to the outer conductor 56 (also see FIG. 2B) of the antenna 203. In this scenario, the outer conductor 56 would operate to electrically connect electrode 712 a to the generator 206 and/or controller 216 (FIG. 3).

While several embodiments of the disclosure have been shown in the drawings, it is not intended that the disclosure be limited thereto, as it is intended that the disclosure be as broad in scope as the art will allow and that the specification be read likewise. Therefore, the above description should not be construed as limiting, but merely as exemplifications of particular embodiments. Those skilled in the art will envision other modifications within the scope and spirit of the claims appended hereto. 

1-20. (canceled)
 21. An ablation device, comprising: an antenna having a proximal end and a distal end; and a trocar including: a shaft operably associated with the distal end of the antenna; a first electrode disposed on a proximal portion of the shaft; and a second electrode forming a distal tip of the shaft and configured for insertion into tissue, wherein the first and second electrodes are longitudinally spaced from one another along a longitudinal axis defined by the shaft.
 22. The ablation device according to claim 21, wherein the antenna extends longitudinally within the shaft of the trocar
 23. The ablation device according to claim 21, wherein the distal end of the antenna is operably coupled to the distal tip of the trocar.
 24. The ablation device according to claim 21, wherein the distal tip of the trocar is conical and configured to penetrate tissue.
 25. The ablation device according to claim 21, wherein the first electrode is ring-like and at least partially encircles the shaft of the trocar.
 26. The ablation device according to claim 21, wherein the antenna further includes an inner conductor electrically connected to the second electrode.
 27. An ablation system, comprising: an antenna having a proximal end and a distal end; a trocar including: a shaft defining a longitudinal axis therethrough and having a distal end operably associated with the distal end of the antenna; a first electrode disposed on a proximal end of the shaft; and a second electrode extending distally from the distal end of the shaft and configured for insertion into tissue, the first and second electrodes longitudinally spaced from one another along the longitudinal axis of the shaft; a power source electrically connected to at least one of the first electrode or the second electrode; and a controller operably associated with the power source, wherein the controller is configured to determine an insertion depth of the trocar in tissue and to control an amount of power output by the power source based on the determined insertion depth.
 28. The ablation system according to claim 27, wherein the antenna extends longitudinally within the shaft of the trocar.
 29. The ablation system according to claim 27, wherein the distal end of the antenna is operably coupled to the second electrode of the trocar.
 30. The ablation system according to claim 27, wherein the second electrode of the trocar is conical and configured to penetrate tissue.
 31. The ablation system according to claim 27, wherein the first electrode is ring-like and at least partially encircles the shaft of the trocar.
 32. The ablation system according to claim 27, wherein the antenna includes an inner conductor electrically connecting the power source and the second electrode.
 33. The ablation system according to claim 32, further comprising a transmission line extending along an outer surface of the shaft of the trocar and electrically connecting the first electrode to the power source. 